CN110235013A - For the dipole antenna component using magnetic nuclear resonance method shooting image - Google Patents
For the dipole antenna component using magnetic nuclear resonance method shooting image Download PDFInfo
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- CN110235013A CN110235013A CN201780070842.6A CN201780070842A CN110235013A CN 110235013 A CN110235013 A CN 110235013A CN 201780070842 A CN201780070842 A CN 201780070842A CN 110235013 A CN110235013 A CN 110235013A
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- G—PHYSICS
- G01—MEASURING; TESTING
- G01R—MEASURING ELECTRIC VARIABLES; MEASURING MAGNETIC VARIABLES
- G01R33/00—Arrangements or instruments for measuring magnetic variables
- G01R33/20—Arrangements or instruments for measuring magnetic variables involving magnetic resonance
- G01R33/28—Details of apparatus provided for in groups G01R33/44 - G01R33/64
- G01R33/32—Excitation or detection systems, e.g. using radio frequency signals
- G01R33/34—Constructional details, e.g. resonators, specially adapted to MR
- G01R33/34038—Loopless coils, i.e. linear wire antennas
-
- G—PHYSICS
- G01—MEASURING; TESTING
- G01R—MEASURING ELECTRIC VARIABLES; MEASURING MAGNETIC VARIABLES
- G01R33/00—Arrangements or instruments for measuring magnetic variables
- G01R33/20—Arrangements or instruments for measuring magnetic variables involving magnetic resonance
- G01R33/28—Details of apparatus provided for in groups G01R33/44 - G01R33/64
- G01R33/32—Excitation or detection systems, e.g. using radio frequency signals
- G01R33/36—Electrical details, e.g. matching or coupling of the coil to the receiver
- G01R33/3642—Mutual coupling or decoupling of multiple coils, e.g. decoupling of a receive coil from a transmission coil, or intentional coupling of RF coils, e.g. for RF magnetic field amplification
- G01R33/365—Decoupling of multiple RF coils wherein the multiple RF coils have the same function in MR, e.g. decoupling of a receive coil from another receive coil in a receive coil array, decoupling of a transmission coil from another transmission coil in a transmission coil array
-
- G—PHYSICS
- G01—MEASURING; TESTING
- G01R—MEASURING ELECTRIC VARIABLES; MEASURING MAGNETIC VARIABLES
- G01R33/00—Arrangements or instruments for measuring magnetic variables
- G01R33/20—Arrangements or instruments for measuring magnetic variables involving magnetic resonance
- G01R33/28—Details of apparatus provided for in groups G01R33/44 - G01R33/64
- G01R33/42—Screening
- G01R33/422—Screening of the radio frequency field
-
- G—PHYSICS
- G01—MEASURING; TESTING
- G01R—MEASURING ELECTRIC VARIABLES; MEASURING MAGNETIC VARIABLES
- G01R33/00—Arrangements or instruments for measuring magnetic variables
- G01R33/20—Arrangements or instruments for measuring magnetic variables involving magnetic resonance
- G01R33/44—Arrangements or instruments for measuring magnetic variables involving magnetic resonance using nuclear magnetic resonance [NMR]
- G01R33/48—NMR imaging systems
- G01R33/4806—Functional imaging of brain activation
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- H—ELECTRICITY
- H01—ELECTRIC ELEMENTS
- H01Q—ANTENNAS, i.e. RADIO AERIALS
- H01Q1/00—Details of, or arrangements associated with, antennas
- H01Q1/27—Adaptation for use in or on movable bodies
- H01Q1/273—Adaptation for carrying or wearing by persons or animals
-
- H—ELECTRICITY
- H01—ELECTRIC ELEMENTS
- H01Q—ANTENNAS, i.e. RADIO AERIALS
- H01Q21/00—Antenna arrays or systems
- H01Q21/06—Arrays of individually energised antenna units similarly polarised and spaced apart
- H01Q21/20—Arrays of individually energised antenna units similarly polarised and spaced apart the units being spaced along or adjacent to a curvilinear path
- H01Q21/205—Arrays of individually energised antenna units similarly polarised and spaced apart the units being spaced along or adjacent to a curvilinear path providing an omnidirectional coverage
-
- G—PHYSICS
- G01—MEASURING; TESTING
- G01R—MEASURING ELECTRIC VARIABLES; MEASURING MAGNETIC VARIABLES
- G01R33/00—Arrangements or instruments for measuring magnetic variables
- G01R33/20—Arrangements or instruments for measuring magnetic variables involving magnetic resonance
- G01R33/28—Details of apparatus provided for in groups G01R33/44 - G01R33/64
- G01R33/32—Excitation or detection systems, e.g. using radio frequency signals
- G01R33/36—Electrical details, e.g. matching or coupling of the coil to the receiver
- G01R33/3628—Tuning/matching of the transmit/receive coil
- G01R33/3635—Multi-frequency operation
-
- G—PHYSICS
- G01—MEASURING; TESTING
- G01R—MEASURING ELECTRIC VARIABLES; MEASURING MAGNETIC VARIABLES
- G01R33/00—Arrangements or instruments for measuring magnetic variables
- G01R33/20—Arrangements or instruments for measuring magnetic variables involving magnetic resonance
- G01R33/28—Details of apparatus provided for in groups G01R33/44 - G01R33/64
- G01R33/32—Excitation or detection systems, e.g. using radio frequency signals
- G01R33/36—Electrical details, e.g. matching or coupling of the coil to the receiver
- G01R33/3678—Electrical details, e.g. matching or coupling of the coil to the receiver involving quadrature drive or detection, e.g. a circularly polarized RF magnetic field
-
- G—PHYSICS
- G01—MEASURING; TESTING
- G01R—MEASURING ELECTRIC VARIABLES; MEASURING MAGNETIC VARIABLES
- G01R33/00—Arrangements or instruments for measuring magnetic variables
- G01R33/20—Arrangements or instruments for measuring magnetic variables involving magnetic resonance
- G01R33/44—Arrangements or instruments for measuring magnetic variables involving magnetic resonance using nuclear magnetic resonance [NMR]
- G01R33/48—NMR imaging systems
- G01R33/4808—Multimodal MR, e.g. MR combined with positron emission tomography [PET], MR combined with ultrasound or MR combined with computed tomography [CT]
- G01R33/481—MR combined with positron emission tomography [PET] or single photon emission computed tomography [SPECT]
-
- H—ELECTRICITY
- H01—ELECTRIC ELEMENTS
- H01Q—ANTENNAS, i.e. RADIO AERIALS
- H01Q9/00—Electrically-short antennas having dimensions not more than twice the operating wavelength and consisting of conductive active radiating elements
- H01Q9/04—Resonant antennas
- H01Q9/16—Resonant antennas with feed intermediate between the extremities of the antenna, e.g. centre-fed dipole
Abstract
A kind of dipole antenna component (1), in the dipole antenna component, at least two dipole antennas (4,5) mutually mechanically connect, however it is not electrically connected to each other, wherein, the dipole antenna intersects in intersection and constructs dipole antenna arm (2a, 2b) from the crosspoint, wherein the dipole antenna arm is arranged in half space.
Description
Technical field
The present invention relates to a kind of dipole antenna components for using magnetic nuclear resonance method shooting image.
Background technique
In the case where magnetic resonance tomography (MRT), the RESONANCE ABSORPTION of proton is usually measured.In order to obtain the letter of supplement
Breath, also shoots following image, and described image is generated using image output method in the case where motivating X core.X core, which is related to NMR, to be had
Source core, the NMR active core are different from proton.The X verification is in known in technical staff.Such as use 23Na core or 31P core.Benefit
The shooting realized with the X core in most cases in time with the shooting realized using the H core dividually into
Row.The measurement of X core generates the complementary information of the in most cases measurement for proton.New old generation about cell viability
The information or conclusion thanked are, for example, to be directed to provide the additional information of X core measurement.However, X nuclear signal in the MRT significantly
Lower than proton signal.Therefore, 1H measurement is usually executed in order to improve the measurement of X core.Scout image and B0Shimming for example for by
In the combined type measurement that the proton channel is realized.The MRT is in medicine at present usually using using between 0.25T and 4T
The instrument of field strength is run.The instrument for clinical field of field strength with 7T is in exploitation.However in principle, can make
It is strong with all magnetic fields, however special license is needed for the operation when necessary.
In order to execute combined type X/1H measurement, the known different MRT coil block for being used to construct dual or triple coordinations
Method.Here, problem is the decoupling of the proton and the X nuclear resounce of the coil.For this purpose, have been known different method and
Device.
The coil is by means of arrester, for example with the passive arrester in most cases on alternate leg
Dual coordination the decoupling realized of birdcage-resonator in open source literature: Shen GX, Wu J f., Boada FE,
Thulborn KR. Experimentally verified, theoretical design of dual-tuned, low-
pass birdcage radiofrequency resonators for magnetic resonance imaging and
magnetic resonance spectroscopy of human brain at 3.0 Tesla. Magn. Reson.
Med. 1999;41:268-275. doi:10.1002/ (SICI) 1522-2594 (199902) 41:2<268::AID-MRM9>
3.0.CO;2-G, Meyerspeer M, Roig ES, Gruetter R, Magill AW. An improved trap
design for decoupling multinuclear RF coils. Magn. Reson. Med. 2013:n/a–n/a.
doi: 10.1002/mrm.24931 und Dabirzadeh A, McDougall MP. Trap design for
insertable second‐nuclei radiofrequency coils for magnetic resonance imaging
and spectroscopy. Concepts Magn. Reson. Part B Magn. Reson. Eng. 2009;35B:
It is illustrated in 121-132. doi:10.1002/cmr.b.20139.
By means of PIN diode, the decoupling realized of independent RF coils of such as two alternately imbalances is in open source literature:
Ha S, Hamamura MJ, Nalcioglu O, Muftuler LT. A PIN diode controlled dual-
tuned MRI RF coil and phased array for multi nuclear imaging. Phys. Med.
Biol. 2010;It is disclosed in 55:2589-2600. doi:10.1088/0031-9155/55/9/011.
Decoupling, such as " butterfly coil " and the surface coils of centering on geometry is in open source literature: Bottomley
PA, Hardy CJ, Roemer PB, Mueller OM. Proton-decoupled, overhauser-enhanced,
spatially localized carbon-13 spectroscopy in humans. Magn. Reson. Med. 1989;
12:348–363. doi: 10.1002/mrm.1910120307., Adriany G, Gruetter R. A half-
volume coil for efficient proton decoupling in humans at 4 tesla. J. Magn.
Reson. San Diego Calif 1997 1997;It is explained in 125:178-184. doi:10.1006/jmre.1997.1113
It states.
Another settling mode is modified resonator structure, the resonance of birdcage for example with additional end loops
Device, as it is in Potter W m., Wang L, McCully K k., Zhao Q. Evaluation of a new 1H/
31P dual-tuned birdcage coil for 31P spectroscopy. Concepts Magn. Reson. Part
B Magn. Reson. Eng. 2013;As described in 43:90-99. doi:10.1002/cmr.b.21239.
Dipole and unipole antenna can use with being combined with surface coils in the system of dual coordination.If the idol
Pole and unipole antenna are arranged in the centre of the surface coils, then faded away due to the magnetic field generation of two conductor assemblies
Coupling magnetic flux (Shajan G, Mirkes C, Buckenmaier K, Hoffmann J, Pohmann R,
Scheffler K. Three-layered radio frequency coil arrangement for sodium MRI of
the human brain at 9.4 Tesla. Magn. Reson. Med. 2015:n/a–n/a. doi: 10.1002/
mrm.25666, Yan X, Wei L, Xue R, Zhang X. Hybrid Monopole/Loop Coil Array for
Human Head MR Imaging at 7 T. Appl. Magn. Reson. 2015:1–10. doi: 10.1007/
s00723-015-0656-5. Yan X, Xue R, Zhang X. A monopole/loop dual-tuned RF coil
for ultrahigh field MRI. Quant. Imaging Med. Surg. 2014;4:225-231).It is described it is single/
Decoupling mechanism between dipole coil and surface coils is therefore also based on the decoupling on geometry.
All methods, in addition to the decoupling on geometry, need additional component being brought into single-frequency in other cases
In the oscillation circuit of coil, this is associated with additional loss.This leads to the reduction of the quality of the HF coil and thus causes
The SNR reduction in terms of received MR signal.Meanwhile the production cost is by higher structure member cost and institute
It states the excessively high coordination of cost of arrester or coordination unit and increases.
Summary of the invention
Therefore, the task of the present invention is a kind of method and a kind of device is provided, the method and device are in a simple manner
And cost-effective realize the decoupling of 1H/X nuclear resounce, and do not interfere the quality of the HF coil herein.The method and institute
Stating device should be able to especially apply below 4 teslas in clinical relevant application field.
From the preamble of claim 1 and claim arranged side by side, task according to the present invention is utilized in right
It is required that characteristic illustrated in feature solve.
From now on, using the apparatus according to the invention to according to the method for the present invention it is possible that clinical related
Field strength in the case where also realized using dipole antenna and surface coils 1H and X nuclear frequency coil resonance it is de-
Coupling.Here, the quality of used HF coil does not reduce.
The scheme that is advantageously improved of the invention illustrates in the dependent claims.
According to the present invention, a kind of dipole antenna component is provided, the dipole antenna component can surround the body of patient
Divide, particular around header arrangement, to motivate or receive the MR signal of different core.
According to the present invention, a kind of component of at least two dipole antennas is provided, the component can surround the body of patient
Partially, such as header arrangement, to motivate or receive MR signal.For this purpose, at least two dipole antennas mutually mechanically connect, so
Without being electrically connected to each other, so that the dipole antenna intersects at a point and surrounds angle each other.Preferably, it surrounds identical
Angle.Thereby, it is possible to be arranged in such a way 2,3,4 or more, such as 16 dipole antennas.It is had more than in a component
In the case where two dipole antennas, the polarized improvement of the circumferential in generated magnetic field can be realized.In a dipole antenna
Be more than in component two dipole antennas be also able to use for parallel image output (as example utilized the downward of k-space
Scan realized rapid image output) or the method for parallel excitation in.
The upward value of the quantity of the dipole antenna is limited only by the aspect of practice.If such as patient should be measured
Head, then as lower component be it is desirable, the component does not limit the facial area of the patient.Two dipole antenna examples
It can such as be arranged with 90 ° of angle arrangement or three antennas with the angle for being respectively 60 °.The dipole antenna from the intersection
The part that point sets out is referred to as dipole antenna arm.The dipole antenna arm can surround same or different angle.
According to the present invention, dipole antenna has at least one curvature, and the curvature causes, and the dipole antenna arm is arranged in
The section or another circular geometry of semicircle, ellipse in half space and are for example formed, but also forms sharp portion.
Dipole antenna can equally have at least two curvature, and curved polygonal in one direction is presented in the curvature, such as described
Dipole antenna can have 90 ° or 95 ° of two bending sections or such as three bending sections, these three bending sections have 60 ° or
65°.In the case where at least two bending sections, the bending section need not be equally big, however for the identical angle of reasons of symmetry
It is preferred.
For all embodiments, the dipole antenna for being fixed on the intersection is answered arranged so that the dipole
Antenna constitutes umbrella portion using the dipole antenna arm, and the umbrella portion can be accommodated as being at side in open cage
The body part of patient, such as head.
Preferably, the dipole antenna of component intersects therebetween on geometry.
Preferably, all dipole antenna arms are equally long, so that the crosspoint of the dipole antenna is in the centre of dipole antenna,
However each arm also can be longer or shorter relative to other arms.
In one preferred embodiment, the longitudinal direction of cylinder is constructed in half space of the dipole antenna arm locating for it
Line, wherein the concept of the cylinder should be so interpreted as under the meaning of mathematics, and the vertical line is parallel to each other and is located in
On one circular plan view or another circular plan view.
In another embodiment, the dipole antenna arm is also capable of forming the vertical line of cone.Such as the cone
Or the cone being truncated surrounds the angle between 45 ° and 120 °.The selection of the angle depends on the evaluation criterion of practice.Suffer from
The body part of person, for example described head should be able to be accommodated by the dipole antenna, and dipole antenna according to the present invention
It should be sized so that, so that the dipole antenna is still cooperated in the MR instrument.
In another embodiment, the dipole antenna being capable of bell-shaped configuration.
The arm of the dipole antenna or the dipole antenna arm include inductively or capacitively, thus to establish for spoke to be received
The resonant frequency penetrated.The dipole antenna can be adjusted to as a result,1The resonant frequency of H core or another seed nucleus.The resonant frequency
Bringing into for that can execute known to technical staff and traditionally inductively or capacitively.
In one preferred embodiment, the dipole antenna has shielding case, and the shielding case is for example placed in institute
It states the intersection of dipole antenna and/or is placed at the dipole arm.Advantageously, the shielding case is placed in the load point
Place, because occurring the highest conservative field E at this.The shielding case is in the bending section of the dipole antenna.
The load point is related to the following point of dipole antenna, and the point is connect via circuit with generator.Each dipole antenna
Line needs load point, the load point can place at any part of the dipole antenna.In the load point and the hair
Intermediate active or passive match circuit can be connected between motor.
Preferably, the shielding case is not open and closes with penetrating through.This has the following advantages that, i.e., in the dipole antenna
Concentric electric field is shielded relative to the research object in the load point of thread elements.This cause again the heating of the research object/
The reduction of SAR.The shielding case leads to the reduction for being originated from the SAR of the conservative field E, and described E usual in the case where MR coil
Lead to the limited of average exciting power.This limits the application range about applicable MRT sequence and typically results in longer
Time of measuring.
In an alternative embodiment, the shielding case can also have for inhibiting the vortex in the MRT to imitate
The opening or pit answered.
Preferably, the shielding case is symmetrically fixed relative to the load point of the dipole antenna, thus from described
The load point of dipole antenna sets out realizes the shielding of the electric field in preferred consistent radius.
The shielding case can have spherical segment, ellipse, preferably with the curved polygonal geometry of a circularity
Or another geometry.
The shielding case has the following advantages that that is, the conservative field E is shielded, and weakens eddy current field.
In another preferred embodiment, the dipole antenna according to the present invention is combined with surface coils, institute
The resonant frequency for stating surface coils and X core is mutually coordinated.
For this purpose, surface coils is preferably so placed at the dipole antenna arm, so that the cross section of the surface coils
It is separated by the projection on dipole antenna arm to the cross section along the axis of symmetry.Corresponding dipole antenna and surface as a result,
Coil decoupling.
One or more surface coils can be arranged along the length of dipole antenna arm.Multiple surface coils, which improve, is used for X
The quantity in the channel of core measurement, this for example can be used in improving the SNR in terms of reception.
Preferably, all dipole antenna arms have at least one coil.This has the following advantages that, i.e., on X core surface
There is not gap along the periphery between coil.Such gap leads to the region with low local sensitivity, i.e., in institute
State SNR bad in region.
The surface coils has capacitor, can adjust the resonant frequency using the capacitor.The resonant frequency
Adjustment is known for technicians.
In one embodiment, all surface coil is adjusted to identical resonant frequency, and the resonant frequency corresponds to
Determining X core to be measured.
In another embodiment, the capacitor can be arranged differently in the case where different surface coils, from
And the capacitor has different resonant frequencies.In the case of this embodiment, the letter of different X core can be measured simultaneously
Number.However in this case, it in most cases needs for example to make X core element by bringing arrester or PIN diode into
It is additionally decoupled to each other.
Table shows the physical data for antenna.
Table 1:
The average field B1+ in the case where identical input power and maximum local (10g) SAR, is normalized into every group
The power of part 1W received, be directed to birdcage coil according to prior art and with and without shielding case according to the present invention
Dipole antenna.
Table 2:
Decoupling between dipole antenna and surface coils.
Detailed description of the invention
In addition, attached drawing shows the embodiment of dipole antenna component according to the present invention.
Wherein:
Fig. 1 is shown: dipole antenna component according to the present invention.
Fig. 2 shows: the not dipole antenna component (in terms of its efficiency compared with the prior art) of surface coils.
Fig. 3 is shown: according to the present invention with shielding case and coil under the arrangement of two different geometries
Dipole antenna component.
Specific embodiment
Band is shown in FIG. 1, and there are four dipole antenna arms 2, the dipole antenna component 1 of 2a, 2b, 2c, in the dipole antenna
The dipole antenna arm 2 in the case where component, 2a, 2b, 2c be respectively provided with capacitive/inductive 3,3a, 3b, 3c ..., 3e.The idol
Pole antenna arm is the following region of dipole antenna 4,5, and the region is at the load point 6 of the dipole antenna by for by institute
The device that connects with stating 7 electrically insulated from one another of dipole antenna is fixed.Shielding case 8 is in the bending section.
Fig. 2 shows a kind of birdcage coil in a) column, wherein shows affiliated B1 efficiency.B) column are shown according to the present invention
Dipole antenna component with shielding case and its B1 efficiency make comparisons.C) column show the dipole antenna group for not shielding case
The identical diagram of part.
In Fig. 3, identical device characteristic appended drawing reference having the same.
A) side shows the dipole antenna component 1 with shielding case 8.The dipole antenna arm 2,2a ... have capacitor 3,3a.
Surface coils 9,9a ... be so arranged at the dipole antenna component 1 so that the surface coils pass through the dipole antenna
Arm 2,2a are separated in centre.The coil equally have capacitor 10,10a ....
B) side is shown as the identical component (with a) with identical appended drawing reference), however the coil 9,9a ...
Imitate the curvature of the dipole antenna arm 2,2a.
Example
The present invention is illustrated by an example below, and this cannot be explained with providing constraints.
It is proposed the component (Fig. 1) being decoupled on a kind of geometry.Due to curved configuration, the dipole antenna is in 200MHz
In the case where with the fundamental vibration on geometry.The intrinsic frequency can be by means of being linked into the dipole structure
Concentric coil is mutually coordinated with clinical field strength.Additionally, there are two the permission of the allocation plan of vertical dipole antenna is orthogonal for band
Operation.Here in shown embodiment, the insulation between the two dipole antennas is 34dB.Fig. 2 shows birdcage lines
The simulation model of circle and curved dual channel dipole antenna and its B1 +Field distribution.Table 1 is described with identical input work
Average B in the case where rate excitation in entire brain1 +(10g) SAR value of field and corresponding part.The curved idol
Pole antenna provides the similar average B in entire brain1 +Field strength, wherein the maximum B1 +It more focuses on described
The upper section of brain.
Optimized embodiment combines the dipole antenna with surface coils, the surface coils and X nuclear resounce phase
Coordinate.The allocation plan is shown in FIG. 3.Table 2 shows the insulation between dipole antenna and surface coils.Maximum coupling
It is combined into -27dB.Decoupling on the geometry of the two components being capable of arrester easy to accomplish and not needing high request.1H
It can be simultaneously in orthogonal lower operation with both system X.Do not occur the deterioration of the SNR of the essence of individual system, because without in addition
(lossy) component for the decoupling must be linked into the circuit.Additionally, the component can also be used
It is tested in decoupling.
Further preferred embodiment is using shielding case below the feed point of the dipole antenna, so as to will be in institute
The conservative electric field shielding generated at stating.Table 1 illustrates shielding action by the local SAR value.Curved dipole antenna
The maximum local SAR of line generation 1.95W/kg.The shielding case makes described value be reduced to 1.65W/kg.Made using having to guide
Material is known well in MRT coil construction to shield electric field.In the preferred embodiment, the shielding is used
In dual purpose: reducing the local SAR and by inhibiting the strong B below the dipole feed point1 +Peak value makes institute
State B1 +Field distribution homogenization.Vortex on the shielding part can be by the sealing of the shielding part and for closing high-frequency electrical
The use of the capacitor of logical circulation road inhibits.
The method is mainly characterized in that curved dipole antenna, the curved dipole antenna is the clinical field strength the case where
The lower use for realizing dipole structure.The dipole of traditional straight line 4T or less due to its length be unable to using.Meanwhile it is described
The bending of dipole antenna does not destroy the symmetrical field distribution of described dipole itself in a manner of being proposed, thus with additional MRT
Decoupling on the geometry of coil keeps feasible.The preferred embodiment is the use of at least two dipole antennas, with
Just the operation under orthogonal is realized.It should be noted that needing at least four on columnar circumference in the dipole component of straight line
A element, to realize circular polarization (8) in the cylinder.Compared to standard birdcage coil, in the dipole antenna
Higher SAR at feed point can be reduced by using there is the shielding case of guide function, and the shielding case can be simply
It is integrated into the coil.The shielding case does not hinder to the eyes of patient and touching for ear, if this is for example in functionality
MRT measurement during if necessary.
The addition (two ends of the surface texture for the curved dipole) of surface texture is on geometry
It is generated in the allocation plan of decoupling, the allocation plan is preferably suited for the MRT realized by means of different core.Make to make
It makes in this component for becoming easy and optimizing SNR, there is no the demands for arrester.There are four surface lines for the band proposed
The allocation plan of circle provides sufficient space for the use of the instrument (earphone, glasses etc.) for functional MRT.The configuration
Scheme is equally best suitable for combined type PET-MR and measures, because playing the metal knot of high-selenium corn for gamma radiation
Structure only occurs in a small amount of area of space and the manipulation of the 1H and x-ray circle system can be in the view of the PET instrument
Field occurs.
It is built with the 4T 1H/31P coil system of dual coordination.The operation under orthogonal of two 60cm long it is curved
Dipole is coordinated with 160MHz phase thus.The coordination of the dipole antenna is realized by means of the coil at the feed point.?
Orthogonal insulation between the two dipoles is 34dB.Conservative electric field at the dipole feed point utilizes uniform metal dish
(shielding case) shields.The B of the birdcage coil of proton1 +Guidance capability and dipole antenna configuration through shielding are in identical quantity
Grade.Compared to birdcage coil, local SAR somewhat higher in the case where the curved dipole antenna, however it is described
Value also allows the reliable use in legal SAR upper limit (UL).
The dipole antenna configuration combines (Fig. 3) with four surface coils, and the surface coils and 31P frequency are in 4T
Mutually coordinate in the case where (64MHz).The surface coils is inductively decoupled to each other.The proton channel and the channel 31P it
Between average decoupling be 49dB in the case where 160MHz and be -8dB(table 2 in the case where 64MHz).The 31P
The SNR of the SNR of surface coils component identical with the size without the dipole antenna is identical.
Table 1
| Birdcage coil | Curved dipole antenna with cover | Curved dipole antenna | |
| The average B on entire head1 +(μ T) | 0.665 | 0.634 | 0.657 |
| Maximum 10g SAR(W/kg) | 1.14 | 1.62 | 1.95 |
The average field B1+ and maximum local (10g) SAR in identical input power, are normalized into every component
The power of 1W received
Table 2
Decoupling between dipole antenna and surface coils is minimum.
Claims (11)
1. dipole antenna component, in the dipole antenna component, at least two dipole antennas are mutually mechanically connected, however not
It is electrically connected to each other,
It is characterized in that,
The dipole antenna intersects in intersection and constructs dipole antenna arm from the crosspoint, wherein the idol
Pole antenna arm is arranged in half space.
2. dipole antenna component according to claim 1,
It is characterized in that,
The dipole antenna component has 3 to 16 dipole antennas.
3. dipole antenna component according to claim 1 or 2,
It is characterized in that,
The curvature representation semicircle of the dipole antenna or the section of ellipse.
4. dipole antenna component according to any one of claim 1 to 3,
It is characterized in that,
The dipole antenna intersects therebetween.
5. dipole antenna component according to any one of claim 1 to 4,
It is characterized in that,
The dipole antenna arm constructs the vertical line of cylinder or cone in the half space locating for it.
6. dipole antenna component according to any one of claim 1 to 5,
It is characterized in that,
The dipole antenna arm includes inductively or capacitively.
7. dipole antenna component according to any one of claim 1 to 6,
It is characterized in that,
The dipole antenna component has shielding case.
8. dipole antenna component according to claim 7,
It is characterized in that,
The shielding case is placed in the intersection of the dipole antenna.
9. dipole antenna component according to any one of claim 1 to 8,
It is characterized in that,
The shielding case is placed at the load point of the dipole antenna component, and the load point is connect with generator.
10. dipole antenna component according to any one of claim 1 to 9,
It is characterized in that,
At least one surface coils is disposed at least one dipole antenna arm.
11. dipole antenna component according to claim 10,
It is characterized in that,
The cross section of the surface coils is separated by the projection on dipole antenna arm to the cross section along the axis of symmetry.
Applications Claiming Priority (3)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| DE102016014978.7A DE102016014978A1 (en) | 2016-12-15 | 2016-12-15 | Dipole antenna arrangement for the acquisition of images with nuclear magnetic resonance methods |
| DE102016014978.7 | 2016-12-15 | ||
| PCT/DE2017/000402 WO2018108193A1 (en) | 2016-12-15 | 2017-11-24 | Dipole antenna assembly for capturing images by means of nuclear magnetic resonance methods |
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| CN110235013A true CN110235013A (en) | 2019-09-13 |
| CN110235013B CN110235013B (en) | 2021-10-29 |
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| CN201780070842.6A Active CN110235013B (en) | 2016-12-15 | 2017-11-24 | Dipole antenna assembly for imaging using nuclear magnetic resonance method |
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| US (1) | US11054491B2 (en) |
| EP (1) | EP3555648B1 (en) |
| JP (1) | JP6944521B2 (en) |
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| DE (1) | DE102016014978A1 (en) |
| WO (1) | WO2018108193A1 (en) |
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|---|---|---|---|---|
| CN113253174A (en) * | 2021-05-13 | 2021-08-13 | 上海联影医疗科技股份有限公司 | Receiving antenna assembly and magnetic resonance device |
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| Publication number | Priority date | Publication date | Assignee | Title |
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| KR102297057B1 (en) * | 2019-06-17 | 2021-09-06 | 가천대학교 산학협력단 | Mono-dipole hybrid array antenna rf coil for magnetic resonance imaging |
| US20210121094A1 (en) * | 2019-10-25 | 2021-04-29 | Hyperfine Research, Inc. | Systems and methods for detecting patient motion during magnetic resonance imaging |
| KR102276107B1 (en) * | 2019-11-14 | 2021-07-13 | 가천대학교 산학협력단 | RF coil based on birdcage coil and dipole antenna for MRI |
| CN112986881B (en) * | 2019-12-17 | 2022-12-20 | 上海联影医疗科技股份有限公司 | Magnetic resonance system calibration method, imaging method and magnetic resonance system |
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- 2017-11-24 JP JP2019525792A patent/JP6944521B2/en active Active
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- 2017-11-24 EP EP17811433.6A patent/EP3555648B1/en active Active
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| CN113253174A (en) * | 2021-05-13 | 2021-08-13 | 上海联影医疗科技股份有限公司 | Receiving antenna assembly and magnetic resonance device |
Also Published As
| Publication number | Publication date |
|---|---|
| US11054491B2 (en) | 2021-07-06 |
| WO2018108193A1 (en) | 2018-06-21 |
| JP2020501636A (en) | 2020-01-23 |
| JP6944521B2 (en) | 2021-10-06 |
| EP3555648B1 (en) | 2020-09-16 |
| EP3555648A1 (en) | 2019-10-23 |
| DE102016014978A1 (en) | 2018-06-21 |
| US20200072919A1 (en) | 2020-03-05 |
| CN110235013B (en) | 2021-10-29 |
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